Selectively expandable composite structures for spinal arthroplasty

ABSTRACT

Embodiments include selectively expandable composite structures useful as spinal arthroplasty devices such as intervertebral disc prostheses. The structures may comprise an outer shell comprised of a non-hydrogel polymer material. The structures also may comprise at least one core positioned within the outer shell. The core may be comprised of a hydrophilic polymer. The core may expand upon hydration, thereby deforming the outer shell. The selectively expandable composite structures may be implanted in a dehydrated form and then expand during re-hydration following implantation.

FIELD OF THE INVENTION

Embodiments of the invention relate to selectively expandable compositestructures for spinal arthroplasty, such as intervertebral discprostheses. More specifically, the selectively expandable compositestructures are capable of water uptake and preferential swelling so thatthe implant will expand at desired locations.

BACKGROUND

The human spine includes intervertebral discs that are located betweenadjacent vertebrae of the spine. The intervertebral discs function tostabilize the spine and distribute forces between vertebrae.Intervertebral discs generally comprise three regions, known as theannulus fibrosis, the nucleus pulposus, and the cartilagenous, or bony,end plates.

The nucleus pulposus retains a gelatinous consistency, and includes ahigh proteoglycan content. The nucleus pulposus further retainsapproximately 70% to 90% water, aiding in its fluid nature. The nucleuspulposus is contained within the annulus fibrosis. The annulus fibrosisretains a more rigid consistency, and is composed primarily of type Iand type II collagen. The annulus fibrosis functions to provideperipheral mechanical support to the intervertebral discs, torsionalresistance, and resistance to the hydrostatic pressures of the nucleuspulposus.

Intervertebral discs may be displaced or damaged due to trauma ordisease. Disruption of the annulus fibrosis may allow the nucleuspulposus to protrude into the vertebral canal, a condition commonlyreferred to as a herniated or ruptured disc. The extruded nucleuspulposus may press on a spinal nerve, resulting in nerve damage, pain,numbness, muscle weakness, and paralysis. Intervertebral discs also maydeteriorate due to the normal aging process. As a disc dehydrates andhardens, the disc space height may be reduced, leading to instability ofthe spine, decreased mobility, and pain.

One way to relieve the symptoms of these conditions is by surgicalremoval of a portion or all of the intervertebral disc. The removal ofthe damaged or unhealthy disc may allow the disc space to collapse,which could lead to instability of the spine, abnormal joint mechanics,nerve damage, and as severe pain.

Researchers therefore have investigated the efficacy of implanting anintervertebral disc prosthesis to replace the damaged portion of thepatient's intervertebral disc. One such prosthesis is an artificialimplantable nucleus replacement device. Nucleus implants are used whenthe nucleus pulposus of the intervertebral disc is damaged but theannulus fibrosis and vertebral end-plates are still sufficientlyhealthy. Nucleus replacement surgery involves removing the damagednucleus pulposus of the intervertebral disc and insertion of the nucleusimplant inside of the retained annulus fibrosis. The nucleus implant canbe a molded polymer-containing device designed to absorb the compressiveforces placed on the spine. For increased strength, the nucleus implantmay be combined with an internal matrix of, for example, bio-compatiblefibers. The retained annulus fibrosis provides tensile strength. Somedesirable attributes of a hypothetical intervertebral disc prosthesisinclude axially compressibility for shock absorbance, excellentdurability to avoid future replacement, and biocompatibility.

The description herein of problems and disadvantages of known apparatus,methods, and devices is not intended to limit the invention to theexclusion of these known entities. Indeed, embodiments of the inventionmay include one or more of the known apparatus, methods, and deviceswithout suffering from the disadvantages and problems noted herein.

SUMMARY OF THE INVENTION

What is needed are improved spinal arthroplasty devices. In particular,an improved intervertebral disc prosthesis is needed. Additionally, anintervertebral disc prosthesis that can better conform to theintervertebral disc space is needed. Embodiments of the invention solvesome or all of these needs, as well as additional needs.

Therefore, in accordance with an embodiment of the present invention,there is provided a selectively expandable composite intervertebral discprosthesis. The prosthesis comprises an outer shell that is comprised ofa non-hydrogel polymer material. Additionally, the prosthesis comprisesat least one core positioned within the outer shell, wherein the core iscomprised of a hydrophilic polymer. The at least one core may expandupon hydration, thereby deforming the outer shell.

In accordance with another embodiment of the present invention, there isprovided a method of treating or preventing a disease or disorderassociated with the spine. The method comprises providing a selectivelyexpandable composite intervertebral disc prosthesis as described herein.The prosthesis may be substantially dehydrated and inserted into anintervertebral disc space. Following insertion, the prosthesis may beallowed to re-hydrate in the intervertebral disc space.

These and other features and advantages of the present invention will beapparent from the description provide herein.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1, embodiments A-E, is a drawing of exemplary selectivelyexpandable composite intervertebral disc prostheses according toembodiments of the invention.

FIG. 2, embodiments A, B, and C, is a drawing of exemplary selectivelyexpandable composite intervertebral disc prostheses according toembodiments of the invention.

FIG. 3, embodiments A and B, is a drawing of two sectional views of anexemplary selectively expandable composite intervertebral discprosthesis

FIG. 4, embodiments A and B, is a drawing of an exemplary selectivelyexpandable composite intervertebral disc prosthesis.

FIG. 5, embodiments A, B, and C, is a drawing of an exemplaryselectively expandable composite intervertebral disc prosthesis.

DETAILED DESCRIPTION OF THE EMBODIMENTS

The following description is intended to convey a thorough understandingof the various embodiments of the invention by providing a number ofspecific embodiments and details involving selectively expandablecomposite structures for spinal arthroplasty. It is understood, however,that the present invention is not limited to these specific embodimentsand details, which are exemplary only. It is further understood that onepossessing ordinary skill in the art, in light of known systems andmethods, would appreciate the use of the invention for its intendedpurposes and benefits in any number of alternative embodiments.

As used throughout this disclosure, the singular forms “a,” “an,” and“the” include plural reference unless the context clearly dictatesotherwise. Thus, for example, a reference to “a spinal implant” includesa plurality of such implants, as well as a single implant, and areference to “a therapeutic agent” is a reference to one or moretherapeutic and/or pharmaceutical agents and equivalents thereof knownto those skilled in the art, and so forth.

As used throughout this description, the expression “selectivelyexpandable” means that the device comprising an outer shell and at leastone core positioned within the outer shell expands in a non-uniformfashion upon hydration. The non-uniform expansion, for example, may becaused by the outer shell constraining the ability of the at least onecore to expand, resulting in preferential expansion in one or moredirections. “Selectively expandable” devices excludes devices such asthe tapered prosthesis described in U.S. Pat. No. 6,132,465.

As used throughout this description, the expression “non-hydrogelpolymer material” denotes any polymer composition that is capable offorming a substantially solid mass, and that is not comprised of ahydrogel polymer. The non-hydrogel polymer materials are capable ofabsorbing less than about 5% by weight of water.

Throughout this description, the term “hydrogel” denotes a polymericmaterial that is capable of absorbing water up to and including itsequilibrium water content. Hydrogels include conventional hydrogelmaterials, as well as xerogel materials, including those disclosed in,for example, U.S. Pat. Nos. 5,047,055, 5,192,326, 5,976,186, 6,264,695,6,660,827, and 6,726,721, the disclosures of each of which areincorporated by reference herein in their entirety.

The expression “hydrophilic polymer” refers to a polymer that is capableof absorbing more than about 10% by weight of water.

Throughout this description, the term “intervertebral disc space” refersto any volume or void between two adjacent vertebrae. The intervertebraldisc space may be the volume inside of the annulus fibrosis of theintervertebral disc. Alternatively, the intervertebral disc space alsomay include the annulus fibrosis itself. The intervertebral disc spacemay include only a portion or the entire volume or void between twoadjacent vertebrae.

Unless defined otherwise, all other technical and scientific terms usedherein have the same meanings as commonly understood by one of ordinaryskill in the art to which this invention belongs. Although any methodsand materials similar or equivalent to those described herein can beused in the practice or testing of the present invention, the preferredmethods, devices, and materials are now described. All publicationsmentioned herein are cited for the purpose of describing and disclosingthe various spinal implants, therapeutic and/or pharmaceutical agents,and other components that are reported in the publications and thatmight be used in connection with embodiments of the invention. Nothingherein is to be construed as an admission that the invention is notentitled to antedate such disclosures by virtue of prior invention.

It is a feature of an embodiment of the present invention to provideselectively expandable composite structures comprising an outer shell ofa non-hydrogel polymer material, and at least one core positioned withinthe outer shell. The core may be comprised of a hydrophilic polymer. Theat least one core may expand upon hydration, thereby deforming the outershell. In this way, the selectively expandable composite structures canbe implanted in a dehydrated form and then attain an expanded form dueto hydration following implantation. The selectively expandablecomposite structures are useful, for example, as spinal arthroplastydevices such as intervertebral disc prostheses, including nucleusreplacements.

The selectively expandable composite structures may be in any desiredshape, in accordance with the guidelines herein. Preferably, thecomposite structures are shaped to function as intervertebral discimplants or devices. For example, the composite structure'scross-sectional shape may be kidney-shaped, C-shaped, oval-like,spherical, rectangular, square, cylindrical, capsule, U-shaped,V-shaped, X-shaped, “0” or donut shaped, and so forth in order toconform to the natural cross-sectional shape of the intervertebral discspace. Additionally, the structures may be any applicable size, inaccordance with the guidelines herein, and preferred sizes are describedherein.

The outer shell of the selectively expandable composite structures maybe comprised of at least one non-hydrogel polymer material. Preferably,at least one of the non-hydrogel polymer materials comprising the outershell is an elastic material. An elastic component of the outer shellmay be desirable because it may enhance deformation of the outer shellwhen the core expands due to hydration. Some suitable non-hydrogelpolymer materials for use in the outer shell include elastomericmaterials, olefin polymers, and thermoplastic silicone polyurethanecopolymers. To the extent that these materials are capable of absorbingmore than about 5% by weight of water, they can be modified by, forexample, cross-linking, etc., to reduce their water absorbing ability towithin the range described herein so as to constitute a non-hydrogelpolymer material.

Suitable elastomeric materials include silicone, polyurethanes, siliconepolyurethane copolymers, polyolefins, thermoplastic elastomers,thermoset elastomers, thermoplastic polymers, thermoset polymers, andcombinations thereof, such as copolymers. Suitable polyolefins includepolyisobutylene rubber and polyisoprene rubber, neoprene rubber, nitrilerubber, vulcanized rubber, and combinations thereof. The vulcanizedrubber described herein may be produced, for example, by a vulcanizationprocess utilizing a copolymer produced as described, for example, inU.S. Pat. No. 5,245,098, from 1-hexene and 5-methyl-1,4-hexadiene.

Suitable olefin polymers also include polymers made from ethylenicallyunsaturated monomers, such as polybutadiene. Olefin polymers typicallyrequire a polymerization catalyst to form the polymer, and polymersderived from ethylenically unsaturated monomers typically require alight or heat activated catalyst to polymerize the polymer.Thermoplastic silicone polyurethane copolymers are particularlypreferred elastomeric materials for use in the invention.

Examples of thermoplastic silicone polyurethane copolymers useful aselastomeric materials include, but are not limited to, siliconepolyetherurethanes; silicone polycarbonateurethane; siliconepoly(tetramethylene-oxide) (PTMO) polyether-based aromatic siliconepolyurethanes; silicone PTMO polyether-based aliphatic polyurethanes;silicone polyurethane ureas; and mixtures and combinations thereof.Suitable thermoplastic silicone polyurethane copolymers are commerciallyavailable, and non-limiting commercially available, suitablethermoplastic silicone polyurethane copolymers comprise, oralternatively consist of, PurSil (including PurSil-10, -20, and -40)(available from Polymertech, Berkley, Calif.), CarboSil (includingCarboSil-10, -20, and -40) (available from Polymertech, Berkley,Calif.), Elast-Eon silicone polyurethanes with silicone content between10% and 50% (available from Aortech Biomaterials, Victoria, Australia),and combinations thereof. Thermoplastic silicone polyurethane copolymersused in the generation of selectively expandable composite structuresmay be non-biodegradable.

In a preferred embodiment, the outer shell may have a differentialcomposition. In other words, the outer shell may be comprised of atleast one non-hydrogel polymer material mixed or combined with one ormore other polymeric materials, including other non-hydrogel polymermaterials. The composition may be varied depending upon the position orlocation in the outer shell in order to provide differential propertiesto the outer shell. For example, the outer shell can be made moremalleable or flexible at its upper and lower surfaces and less malleableor flexible along its periphery by varying the composition of the outershell, for example, by using more elastic polymers at its upper andlower surfaces and less elastic polymers at its periphery. Doing so mayfacilitate the selective or preferential expansion of the device uponhydration of its core.

Because the outer shell may comprise at least one polymeric material, atleast one of which is elastic, the outer shell may possess an intrinsicvolume, regardless of the state of hydration of the selectivelyexpandable composite implant. In a preferred embodiment, the hydrophilicpolymer that comprises the core is no more than about 75%, and morepreferably no more than about 60%, and most preferably no more thanabout 50% of the total volume of the selectively expandable compositestructure in its de-hydrated state. This may be advantageous because,were the composite structure to de-hydrate in situ, at least the outershell would retain its intrinsic volume, and therefore the compositestructure may continue to at least partially support the disc spaceheight and articulation of the vertebrae between which it is implanted.Comparatively, a composite structure where the volume primarily is afunction of the hydrophilic polymer may almost completely deflate if itwere to de-hydrate in situ, possibly leading to catastrophic diskcollapse and other inappropriate disc mechanics. In another preferredembodiment, the increase in volume of the selectively expandablecomposite structure is no more than about 3 times, more preferably nomore than about 2.5 times, and most preferably no more than about 2times the de-hydrated volume. Therefore, were the composite structure tode-hydrate in vivo, the structure still may retain at least half of itshydrated volume, which may help to prevent catastrophic disc collapseand failure.

Nevertheless, an increase in volume via hydration following implantationmay be useful, for example, in order to improve the fit and geometry ofthe selectively expandable composite structure. Preferably, thecomposite structure may be implanted with a volume and/or height atleast slightly less than the volume and/or height of the intervertebraldisc space. This may facilitate insertion of the composite structure byensuring that the dimensions of the composite structure are such thatthey it can fit within the confines of the intervertebral disc space.Upon implantation, the structure preferably hydrates by absorbing waterfrom surrounding bodily fluids or applied solutions and, because thecore comprises a hydrophilic polymer, the composite structure expands.The expansion of the composite structure preferably may result in thestructure filling at least 90%, more preferably at least 95%, even morepreferably at least 99%, and most preferably at least 100% of the volumeof the intervertebral disc space into which it is implanted. Also, whenexpanded, the composite structure preferably at least equals the widthand height of the natural disc space. In some instances where disc spaceheight is to be restored, the expanded composite implant preferablyincreases the disc height by pushing on the vertebral endplates of theadjacent vertebrae. Generally, a structure that expands uponimplantation, such as the composite structures herein, may lead toimproved fit and geometry of the structure, in turn leading to increasedmaximum load-bearing, stress transfer, and bonding of the structure tothe intervertebral disc space.

Besides increasing the volume of the selectively expandable compositestructure, the core may be useful to absorb the load and shock placedupon the prosthesis when implanted between adjacent vertebrae. Forexample, as the hydrophilic polymer(s) that comprise the core expandduring hydration, the core may become more compliant as a result of itswater uptake. A more compliant core may serve to more readily absorb thestresses placed on the composite structure. This may be advantageous tosimulate or imitate the functioning of the endogenous intervertebraldisc.

The ability of the composite structure to expand upon hydration may be afunction of the hydrophilic polymers that comprise the at least onecore. Hydrophilic polymers useful in forming the expandable compositestructures of embodiments of the invention include any applicable nowknown or later discovered hydrophilic polymers that are capable ofabsorbing more than about 10% by weight of water, preferably more thanabout 15% by weight of water, and more preferably more than about 50% byweight of water, in accordance with the guidelines provided herein. Someexemplary materials for use in the at least one core include hydrogelsand polyelectrolytes. To the extent that these materials are capable ofabsorbing less than about 10% by weight of water, they can be modifiedto increase their water absorbing ability to within the range describedherein, so as to constitute a hydrophilic polymer. In an alternativeembodiment, the core may comprise more than one hydrophilic polymer. Thehydrophilic polymers may be present in the core as a blend, mixture, orin a heterogeneous configuration.

Non-limiting examples of hydrophilic polymers include, but are notlimited to, polyacrylamide; polyacrylic acid; polyvinylpyrrolidone;copolymers of ethyleneoxide and propyleneoxide or hyaluronic acid;naturally-occurring materials such as collagen, gelatin, albumin,keratin, elastin, silk, hyaluronic acid and derivatives thereof,proteoglycan, glucomannan gel, and polysaccharides such as cross-linkedcarboxyl-containing polysaccharides; and combinations thereof.

In another preferred embodiment, polyelectrolytes can be used as thehydrophilic polymer that comprises the at least one core, or are addedin combination with the hydrophilic polymer to further enhance thehydrophilic nature of the core of the expandable composite structures.Non-limiting examples of polyelectrolytes that may be added to oralternatively comprise the core of hydrophilic polymer include, but arenot limited to, members of the following systems: proteins, nucleicacids, sulfonated styrene, polyacrylic acids, polymethacrylic acid,polystyrene sulfate, carboxymethylcellulose, Xantham gum, pectins,polyallylamine hydrochloride, carrageenan, and mixtures and combinationsthereof. Polyelectrolytes are well known in the art, and one skilled inthe art will appreciate still other examples of polyelectrolytes thatmay be used in the embodiments described herein.

Polyelectrolytes may be added to the hydrophilic polymer inconcentrations comprising, or alternatively consisting of, about 5-100%by weight of the hydrophilic polymer, when used in combination withanother hydrophilic polymer. The polyelectrolyte preferably is presentin an amount ranging from about 5-25% (by weight), based on the weightof the hydrophilic polymer.

In another embodiment, the hydrophilic polymer may be a hydrogel.Suitable hydrogels include natural hydrogels and those formed frompolyvinyl alcohol; polyacrylamides; polyacrylic acid;poly(acrylonitrile-acrylic acid); polyurethanes; polyethylene glycol;polyethyleneoxide; poly(N-vinyl-2-pyrrolidone); polyacrylates such aspoly(2-hydroxy ethyl methacrylate) and copolymers of acrylates withN-vinyl pyrrolidone; N-vinyl lactams; acrylamide; polyurethanes; othersimilar materials that form a hydrogel; and combinations thereof. Thehydrogel materials further may be cross-linked to provide additionalstrength to the outer shell.

In another preferred embodiment, additives may be added to thehydrophilic polymer in order to modify or enhance the water absorptionbehavior of the core. For example, additives such as sodium chloride,calcium chloride, magnesium chloride, magnesium sulfate, potassiumsulfate, potassium chloride, sodium sulfate, sodium acetate, ammoniumphosphate, ammonium sulfate, calcium lactate, magnesium succinate,sucrose, glucose, and fructose may be added to the hydrophilic polymerin the core in order to increase the hydrophilicity of the core.

The at least one core comprising a hydrophilic polymer may be present inany number of physical configurations, including a single piece,multiple pieces, chunks, granules, flakes, pellets, cylinders, strips,spheres, microspheres, powders, beads, capsules, and particulates.Additionally, the core may be mixtures and combinations of thesedifferent physical configurations. For example, the core may comprisesmultiple solid pieces mixed with granules, which may fill the voids inbetween the multiple solid pieces. Furthermore, the core may be eithersolid or porous. For example, if the core comprises multiple pieces, themultiple pieces may individually be solid or porous pieces. A porous orsemi-porous core may be desirable to serve as a reservoir fortherapeutic agents, pharmaceutical agents, growth factors, andradiopaque agents. Preferably, if at least a portion of the core isporous, the porous portion comprises no more than about 75% by volume ofvoids, more preferably no more than about 60% by volume of voids, andmost preferably no more than about 50% by volume of voids.

If desired, the core may be formed before, during, or after implantationof the outer shell. For example, the core typically may be implantedwith the outer shell (i.e. the core is already positioned within theouter shell when the outer shell is delivered to the implant site).However, in some instances it may be desirable to implant the outershell portion of the selectively expandable device separately from theat least one core. Then, the at least one core may be delivered insideof the outer shell. For example, the hydrophilic polymer(s) thatcomprise the core may be delivered by cannula into the interior of theouter shell, for example, through a collapsible valve positioned in theouter shell. The hydrophilic polymer advantageously may be heated inorder to reduce its viscosity in preparation of delivery to the interiorof the outer shell. Subsequent delivery of the hydrophilic polymercomprising the core after implantation of the outer shell may bedesirable in order to reduce the cross-section of the device duringimplantation. By implanting the device as two separate components, eachhaving a cross-section smaller than the whole, delivery of the device tothe confines of the intervertebral disc space may be facilitated.

In another embodiment of the invention, the selectively expandablecomposite structures may assume any appropriate geometry or size forimplantation into the intervertebral disc space. For example, theselectively expandable composite structures preferably may be from about3 mm to about 15 mm in height so as to accommodate a range ofintervertebral disc space heights. The selectively expandable compositestructures also preferably may range in volume from about 0.5milliliters to about 8 milliliters in a hydrated state so as toaccommodate a range of intervertebral disc space volumes. One who isskilled in the art will appreciate the myriad geometries and sizes thatthe selectively expandable composite structures may take, in accordancewith the guidelines herein.

In a preferred embodiment, the outer shell may be designed so that watercan penetrate through the outer shell to reach the at least one core ofhydrophilic polymer positioned within the shell. Penetration of water tothe at least one core may be desirable because hydration of the core maycause it to expand, thereby deforming the outer shell in a selectivemanner and increasing the overall volume of the composite structure.Penetration of water to the at least one core may occur in anyapplicable fashion according to the guidelines herein, and severalexemplary methods are described herein.

In one example, it may be preferred that the outer shell comprise ahydrophilic component mixed with the non-hydrogel polymer material. Byabsorbing moisture from the environment surrounding the selectivelyexpandable composite structure, the hydrophilic component of the outershell can deliver water to the at least one core positioned within theshell. Preferably, the hydrophilic component in the outer shell may befrom about 1% to about 25% by weight of the mixture of non-hydrogelpolymer material and hydrophilic component. The hydrophilic polymers,including polyelectrolytes and hydrogels, described herein in relationto the hydrophilic core also are suitable hydrophilic components for usein the outer shell.

In another preferred embodiment, the outer shell may comprise aplurality of perforations of sufficient size and number to permit fluidsto percolate through the shell and contact at least a portion of the atleast one core. The perforations in the outer shell may be described asslits or cuts. Preferably, the perforations are of sufficient depth tocontact or even extend into the at least one core positioned with theouter shell. In this manner, a physical pathway may be provided so thatfluids in the environment surrounding the composite structure canpenetrate to and hydrate the at least one core.

The outer shell also may be at least partially porous in preferredembodiments of the invention. Again, pores in the shell may providephysical routes for fluids to penetrate to and hydrate the at least onecore. The pores may be located throughout the outer shell or may bepositioned only in portions of the shell that are adjacent to corespositioned within the shell. Also, the density and depth of pores in theshell may vary by location or position. For example, pores may beconcentrated and deeper in portions of the shell adjacent to thehydrophilic cores that are to be hydrated.

Any pores or, alternatively, perforations in the outer shell of theselectively expandable composite structures preferably are sized in sucha manner as to preclude migration of the core material outside of thecomposite structure. For example, if the material comprising the core isgranular in nature, the pores or perforation in the outer shellpreferably are small enough to prevent migration of the granular corematerial outside of the composite structure. This applies equally to acore, for example, comprising a solid piece, multiple solid pieces,several chunks, granules, flakes, pellets, cylinders, strips, spheres,microspheres, powders, or mixtures and combinations thereof.

The composite structures also may comprise at least one conduit thatconnects the at least one core with a surface of the prosthesis. Theconduits may comprise a hydrophilic polymer. Preferably, the conduitsmay comprise the same hydrophilic polymer of which the at least one coreis comprised. The conduits may provide a route by which moisture may bewicked from the environment surrounding the composite structure to theat least one core positioned within the outer shell. Exemplary conduitsare illustrated in FIG. 5, embodiments A, B, and C. As can be seen, thecores are connected to the surface of the device by one or more conduitsof hydrophilic material. Preferably, as in embodiment B, each core (ifmore than one) within the outer shell is connected by a conduit to thesurface of the device. If desired, more than one conduit may connect acore to the surface (e.g. embodiment C). Also, if desired, some coresmay be connected by conduits, whereas others are not (e.g. embodimentD). The conduits may enhance fluid exchange with the environment inorder to accelerate hydration of the core(s) within the outer shell.

Upon hydration, the composite structures preferably expand in aselective manner. The selective expansion of the composite structuresmay depend upon several different variables, including the type ofhydrophilic polymer that comprises the at least one core; the type ofnon-hydrogel polymer material that comprises the outer shell; theconcentrations of non-hydrogel polymer material and hydrophilicmaterial, respectively, in the outer shell and the at least one core;the shape of the outer shell and the at least one core; the position(s)within the outer shell at which the at least one core is located; and soforth. In a preferred embodiment, these variables may be controlled inorder to produce swelling or expansion of the composite structures uponhydration in selected areas or portions of the structures. In this way,the final configuration of the expanded structure can be controlled toproduce a desired configuration, topography, geometry, or shape. Forexample, expansion can be controlled so that the anterior portion of acomposite structure to be used as an intervertebral disc prosthesisexpands more than the posterior portion. A selectively expandableintervertebral disc prosthesis with preferential anterior expansion maybe useful to correct or preserve lordosis of the spine.

In a preferred embodiment, the composite structures provided byembodiments of the invention are configured to function asintervertebral disc prostheses, such as nucleus replacements andreplacements for the entire intervertebral disc. Intervertebral discprostheses according to this embodiment optionally may comprisesupplemental components, such as vertebral endplate contacting elements,in order to increase their utility for treating disorders of the spine.

FIG. 1, embodiments A-E, illustrates exemplary intervertebral discprostheses according to embodiments of the invention. The viewsillustrated are cross-sections of intervertebral disc prostheses andillustrate how placement, size, and shape of the hydrophilic core canaffect the expansion of the composite structure upon hydration.Embodiments B, C, and E, for example, illustrate selectively expandablecomposite structures that are useful for the correction and maintenanceof spinal curvature because one end of the prosthesis expands to agreater height than does the other end. In embodiments B and C, forexample, the selective expansion is due to the shape of the hydrophiliccore. In embodiment E, the selective expansion is due to the placementof the hydrophilic core at one end only of the composite structure.

Embodiments A and D illustrate selectively expandable compositestructures that are useful for engagement with hemispherical vertebralendplates because they have a greater height at the center of thestructure than at the periphery. As can be seen in embodiment A, thismay be the result of the outer shell being thinner at the top and bottomof the composite structure, but thicker on the sides or periphery of thecomposite structure. Also, as can be seen in embodiment D, this may bethe result of the dome-like shape of the hydrophilic core within theouter shell. Selectively expandable composite structures having eitherconcave or convex top and bottom surfaces may be useful for mating withconvex or concave surfaces, respectively, of upper and lower vertebralendplates between which the selectively expandable composite structuresare to be positioned. For example, Embodiments A and D illustrateselectively expandable composite structures having convex upper andlower surfaces. Therefore, these structure may be appropriate forimplantation between upper and lower vertebral endplates having concavesurfaces.

In another embodiment, the selectively expandable composite structures,when in a de-hydrated state, have a size and geometry primarily dictatedby the size and geometry of the outer shell of the composite structures.Therefore, as illustrated in FIG. 1, embodiments A-E, the exemplarycomposite structures are all rectangular in profile in their de-hydratedstate. However, upon hydration, the outer shell preferably isselectively deformed according to the shape of the hydrophilic innercore. Therefore, as illustrated in FIG. 1, the outer shells of theexemplary composite structures, upon hydration, are deformed accordingto the shape of the inner cores. For example, the inner core inembodiment B is triangular in profile and causes the outer shell, uponhydration, to deform into a more triangular shape. In other words, in apreferred embodiment the shape of the composite structures uponhydration in part may be determined by the shape of the inner core,among other factors. Preferably, the shape of the composite structure inits de-hydrated state corresponds to a preferred insertionconfiguration, and the shape of the composite structure in its hydratedstate corresponds to a preferred configuration for long-term placementand funcationality in the intervertebral disc space.

In a preferred embodiment, more than one hydrophilic polymer core ispositioned within the outer shell. The cores may be positioned atselected regions of the composite structures in which expansion isdesired. An exemplary selectively expandable intervertebral discprosthesis having multiple cores placed at selected positions within theouter shell is illustrated in FIG. 2, embodiment A. Embodiment Aillustrates a selectively expandable composite intervertebral discprosthesis with multiple hydrophilic polymer cores with circularcross-sections within the outer shell. The multiple hydrophilic coresare disposed at various positions within the outer shell. When they arehydrated, the cores may cause the shell to be selectively deformed atthese positions.

FIG. 2, embodiments B and C, illustrate other selectively expandablecomposite intervertebral disc prostheses comprising an outer shell and acore comprised of a hydrophilic polymer positioned within the outershell. In both embodiments, the core is located at the anterior portionof the intervertebral disc prosthesis. Therefore, upon hydration, theprosthesis will selectively expand at the anterior portion, which may beuseful to correct and maintain proper curvature in the spine.

FIG. 3, embodiments A and B, illustrates another intervertebral discprosthesis according to embodiments of the invention. An outer shell 30and a hydrophilic core 31 positioned within the shell are provided. Inembodiment B, it can be seen that the thickness of the outer shell mayvary depending upon its position in the prosthesis. For example, at theperiphery of the prosthesis, the outer shell 30(a) is thicker than it isat the top and bottom of the prosthesis 30(b). As mentioned, the shapeof the outer shell can affect the behavior of the composite structuresduring expansion. For example, where the outer shell is thicker at theperiphery of the composite structures than at the top and bottom, as isexemplary illustrated in FIG. 3, embodiment B, the composite structuremay expand more in the vertical direction than the horizontal orperipheral direction when hydrated. Therefore, preferential expansion inthe vertical direction may be achieved. In generally, varying thethickness of the outer shell depending upon its position within thedevice may effect the expandability of the device. Portions of thedevice where expansion upon hydration is desired, for example, may havea thinner outer shell, whereas portions of the device where expansion isnot desired and is to be limited may have a thicker outer shell.

Another method by which the expansion of the composite structures duringhydration may be controlled is by varying the concentration andcomposition of the non-hydrogel polymeric material and hydrophilicpolymer comprising, respectively, the outer shell and the at least onecore of the composite structures. For example, by diluting thehydrophilic polymer which comprises the at least one core with anon-hydrophilic polymer, the expandability of the composite structuresmay be decreased. Also, by mixing the non-hydrogel polymeric materialcomprising the outer shell with more or less compliant polymers, theexpandability of the composite structures may be, respectively,increased and decreased. In a preferred embodiment, for example, thehydrophilic core may comprise from about 1% to about 50% of anon-hydrophilic polymer in order to enhance the core's mechanicalproperties. One skilled in the art will appreciate the wide variety ofpolymeric components that may be mixed with the hydrophilic polymercomprising the core and the non-hydrogel polymer material comprising theouter shell.

Another method by which the expandability of the composite structuresmay be regulated is by the inclusion of one or more reinforcing elementsin the outer shell. Reinforcing elements applicable to the compositestructures according to embodiments of the invention include, but arenot limited to, metallic fibers, carbon fibers, metal meshes, and wovenfiber inserts. For example, metallic, ceramic, or polymeric fibers incontinuous, discontinuous, woven, non-woven, and braided fabrics may beplaced on the surface of the device. Alternatively, such structures maybe used as a band around the perimeter or periphery of the device. Suchstructures also may be embedded into the shell or core of the compositestructures. One of skill in the art will appreciate other applicablereinforcing elements, in accordance with the guidelines provided herein.Generally, the reinforcing elements may be positioned at portions of theouter shell where expansion is to be limited. Therefore, the expansionof the selectively expandable composite structure may be directed byplacing reinforcing elements at or in portions of the outer shell wereexpansion is desired to be limited or prevented.

In general, inclusion of reinforcing elements, varying the thickness ofthe outer shell, and varying the composition of the outer shell and/orhydrophilic core of the device may be categorized as methods to vary themodulus of elasticity of the device. Varying the modulus of elasticityof portions of the device depending upon the portions' positions in thedevice may be desirable as a way to encourage selective expansion uponhydration of the device. Selective expansion of implantable devices maybe desirable to create structures of more complex geometry for betterclinical outcomes, as discussed herein.

In another preferred embodiment, the selectively expandable compositestructures may be combined with additional components to form a morecomplex implantable device. For example, a selectively expandablecomposite structure may function as the nucleus of a total discreplacement (TDR) device that comprises other components in addition toa selectively expandable composite structure. In a preferred embodiment,vertebral endplate contacting elements are positioned on the upper andlower surfaces of the device. Endplate contacting elements preferablymay be composed of a medical metal or alloy and may be configured toengage the vertebral endplates of the vertebrae between which theselectively expandable composite structure is to be implanted.

Besides imparting expandability to the composite structures, the atleast one hydrophilic core may act as a reservoir to retain and delivervarious therapeutics, pharmaceutical agents, growth factors, andradiopaque materials. The therapeutics, pharmaceutical agents, growthfactors, and radiopaque materials preferably may be controllablyreleased from the hydrophilic core. In other words, the core mayfunction to slowly release the materials disposed therein followingimplantation. Conduits, slits, pores, or a hydrophilic component in theouter shell may act to allow the therapeutics to exit the core of thecomposite structure. Additionally, therapeutics, pharmaceutical agents,growth factors, and radiopaque materials may be mixed with the outershell in order to impart additional biologically advantageouscharacteristics to the outer shell or to aid in identifying andpositioning the device during implantation.

For example, the non-hydrogel polymer materials and hydrophilic polymersmay comprise therapeutics such as pharmacological agents, biologicalagents, and growth factors. Examples of pharmacological agents,biological agents, and growth factors include, but are not limited to,antibiotics, analgesics, anti-inflammatory drugs, steroids, anti-viraland anti-retroviral compounds, therapeutic proteins or peptides, andtherapeutic nucleic acids (as naked plasmid or a component of anintegrating or non-integrating gene therapy vector system).

Antibiotics useful with the selectively expandable composite structuresinclude, but are not limited to, aminoglycosides, amoxicillin,beta-lactamases, beta-lactam (glycopeptide), clindamycin,chloramphenicol, cephalosporins, ciprofloxacin, erythromycin,fluoroquinolones, macrolides, metronidazole, penicillins, quinolones,rapamycin, rifampin, streptomycin, sulfonamide, tetracyclines,trimethoprim, trimethoprim-sulfamthoxazole, and vancomycin. In addition,one skilled in the art of implant surgery or administrators of locationsin which implant surgery occurs may prefer the introduction of one ormore of the above-recited antibiotics to account for nosocomialinfections or other factors specific to the location where the surgeryis conducted. Accordingly, the invention further contemplates that oneor more of the antibiotics recited supra, and any combination of one ormore of the same antibiotics, may be included in the selectivelyexpandable composite structures of the invention.

Immunosuppressives may be administered with the selectively expandablecomposite structures according to the embodiments. Suitableimmunosuppressive agents that may be administered include, but are notlimited to, steroids, cyclosporine, cyclosporine analogs,cyclophosphamide, methylprednisone, prednisone, azathioprine, FK-506,15-deoxyspergualin, and other immunosuppressive agents that act bysuppressing the function of responding T cells. Other immunosuppressiveagents that may be administered in combination with the selectivelyexpandable composite structures include, but are not limited to,prednisolone, methotrexate, thalidomide, methoxsalen, rapamycin,leflunomide, Bredinin™ (mizoribine), brequinar, deoxyspergualin, andazaspirane (SKF 105685), Orthoclone OKT™ 3 (muromonab-CD3). Sandimmune™,Neoral™, Sangdya™ (cyclosporine), Prograf™ (FK506, tacrolimus),Cellcept™ (mycophenolate motefil, of which the active metabolite ismycophenolic acid), Imuran™ (azathioprine), glucocorticosteroids,adrenocortical steroids such as Deltasone™ (prednisone) and Hydeltrasol™(prednisolone), Folex™ and Mexate™ (methotrxate), Oxsoralen-Ultra™(methoxsalen) and Rapamuen™ (sirolimus). Other drugs useful with thecomposite structures include anti-cytokines such as anti-tumor necrosisfactor alpha (anti-TNF alpha), anti-interleukin 2 (anti-IL2), anti-IL4,anti-IL10, anti-IL18, etc.

Therapeutic polynucleotides or polypeptides (hereinafter “therapeutics”)may be used with the selectively expandable composite structures. Thetherapeutics may be administered as proteins, peptides, and therapeuticnucleic acids, and may be administered as full length proteins, matureforms thereof, and domains thereof, as well as the polynucleotidesencoding the same. Examples of therapeutic polypeptides include, but arenot limited to, Bone Morphogenetic Proteins (BMPs), including BMP-1,BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, BMP-7, BMP-8, BMP-9, BMP-10, BMP-11,BMP-12, BMP-13, BMP-15, BMP-16, BMP-17, and BMP-18; Vascular EndothelialGrowth Factors (VEGFs), including VEGF-A, VEGF-B, VEGF-C, VEGF-D andVEGF-E; Connective Tissue Growth Factors (CTGFs), including CTGF-1,CTGF-2, and CTGF-3; Osteoprotegerin, Transforming Growth Factor betas(TGF-bs), including TGF-b-1, TGF-b-2, and TGF-b-3; and Platelet DerivedGrowth Factors (PDGFs), including PDGF-A, PDGF-B, PDGF-C, and PDGF-D.The polynucleotides encoding the same also may be administered as genetherapy agents.

In a particularly preferred embodiment, the selectively expandablecomposite structures may comprise antagonists to either themyelin-associated glycoprotein (MAG) or Nogo-A, the largest transcriptof the recently identified nogo gene (formerly called NI-220), which areboth present in CNS myelin and have been characterized as potentinhibitors of axonal growth. For example, Nogo-A acts as a potentneurite growth inhibitor in vitro and represses axonal regeneration andstructural plasticity in the adult mammalian CNS in vivo. In anotherembodiment, antagonists to both MAG and Nogo-A are co-administered tothe patient. In this preferred embodiment, the selectively expandablecomposite structures of the invention are used as implants forintervertebral discs that are adjacent locations of spinal cord injury,and may also replace a damaged or infected native nucleus pulposus. Inthis embodiment, the inhibitory activity of the antagonist(s) to theactivity of MAG and Nogo-A may aid in the regeneration of damaged spinalnerve tissue, and the selectively expandable composite structure servesas a local reservoir of therapeutic antagonist(s) to aid in the growthof damaged spinal tissue. Antagonists of MAG and Nogo-A may take theform of monoclonal antibodies, anti-sense molecules, small moleculeantagonists, and any other forms of protein antagonists known to thoseof skill in the art.

In this embodiment, therapeutic polypeptides or polynucleotides ofNinjurin-1 and Ninjurin-2 may further be administered alone or inconjunction with one or more MAG or Nogo-A antagonists, as a componentof the selectively expandable composite structures. Ninjurin-1 andNinjurin-2 are believed to promote neurite outgrowth from primarycultured dorsal root ganglion neurons. Ninjurin-1 is a gene that isup-regulated after nerve injury both in dorsal root ganglion (DRG)neurons and in Schwann cells. The full-length proteins, mature forms, ordomains of the full-length proteins thereof may be administered astherapeutics, as well as the polynucleotides encoding the same.

Embodiments of the invention also include a method of treating spinalcord injury using the selectively expandable composite structuresdescribed herein as a reservoir for therapeutic agents that promote thegrowth of injured spinal cord tissue or damaged nerves. The methodincludes administering at least one or more, including all, of theabove-recited therapeutics as a component of the selectively expandablecomposite structures of the invention. In one embodiment, thenon-hydrogel polymer material and hydrophilic polymer may be admixedwith the therapeutic agents. In another embodiment of the invention, thetherapeutic agents are applied to the selectively expandable compositestructures prior to implantation of the structures. The therapeuticagents may be administered to the selectively expandable compositestructures in any number of suitable fluids, such as for example, water,saline solution, and calcium phosphate solution.

Methods of producing therapeutic polynucleotides and polypeptides thatmay be co-administered with the selectively expandable compositestructures are well known to one of skill in the art. Vectors containingthe therapeutic polynucleotides recited supra, host cells, and theproduction of therapeutic polypeptides by recombinant techniques can beused to make the therapeutic polynucleotides and polypeptides. Thevector may be, for example, a phage, plasmid, viral, or retroviralvector. Retroviral vectors may be replication competent or replicationdefective. In the latter case, viral propagation generally will occuronly in complementing host cells.

The polynucleotides may be joined to a vector containing a selectablemarker for propagation in a host. Generally, a plasmid vector isintroduced in a precipitate, such as a calcium phosphate precipitate, orin a complex with a charged lipid. If the vector is a virus, it may bepackaged in vitro using an appropriate packaging cell line and thentransduced into host cells. Useful vectors include, but are not limitedto, plasmids, bacteriophage, insect and animal cell vectors,retroviruses, cosmids, and other single and double-stranded viruses.

The polynucleotide insert may be operatively linked to an appropriatepromoter, such as the phage lambda PL promoter, the E. coli lac, trp,phoA and tac promoters, the SV40 early and late promoters and promotersof retroviral LTRs, to name a few. Other suitable promoters will beknown to the skilled artisan. The expression constructs may furthercontain sites for transcription initiation, termination, origin ofreplication sequence, and, in the transcribed region, a ribosome bindingsite for translation. The coding portion of the transcripts expressed bythe constructs preferably may include a translation initiating codon atthe beginning and a termination codon (UAA, UGA or UAG) appropriatelypositioned at the end of the polypeptide to be translated.

The expression construct may further contain sequences such as enhancersequences, efficient RNA processing signals such as splicing andpolyadenylation signals, sequences that enhance translation efficiency,and sequences that enhance protein secretion.

Expression systems and methods of producing therapeutics, such asrecombinant proteins or protein fragments, are well known in the art.For example, methods of producing recombinant proteins or fragmentsthereof using bacterial, insect or mammalian expression systems are wellknown in the art. (See, e.g., Molecular Biotechnology: Principles andApplications of Recombinant DNA, B. R. Glick and J. Pasternak, and M. M.Bendig, Genetic Engineering, 7, pp. 91-127 (1988), for a discussion ofrecombinant protein production).

The expression vectors preferably will include at least one selectablemarker. Such markers include dihydrofolate reductase, G418 or neomycinresistance for eukaryotic cell culture and tetracycline, kanamycin, orampicillin resistance genes for culturing in E. coli and other bacteria.Representative examples of appropriate host cells for expressioninclude, but are not limited to, bacterial cells such as E. coli,Streptomyces and Salmonella typhimurium cells; fungal cells such asPichia, Saccharomyces and other yeast cells; insect cells such asDrosophila S2 and Spodoptera Sf9 and Sf21 cells; animal cells such asCHO, COS, 293, and Bowes melanoma cells; and plant cells. Appropriateculture mediums and conditions for the above-described host cells areknown in the art.

Examples of vectors for use in prokaryotes include pQE30Xa and other pQEvectors available as components in pQE expression systems (commerciallyavailable from QIAGEN, Inc., Valencia, Calif.); pBluescript vectors,Phagescript vectors, pNH8A, pNH16a, pNH18A, and pNH46A (commerciallyavailable from Stratagene Cloning Systems, Inc., La Jolla, Calif.); andChampion™, T7, and pBAD vectors (commercially available from Invitrogen,Carlsbad, Calif.). Other suitable vectors will be readily apparent tothe skilled artisan.

Introduction of the construct into the host cell can be effected bycalcium phosphate transfection, DEAE-dextran mediated transfection,cationic lipid-mediated transfection, electroporation, transduction,infection, and other methods. Such methods are described in manystandard laboratory manuals, such as Davis et al., Basic Methods InMolecular Biology (1986).

A polypeptide of an embodiment can be recovered and purified fromrecombinant cell cultures by well-known methods including ammoniumsulfate or ethanol precipitation, acid extraction, anion or cationexchange chromatography, phosphocellulose chromatography, hydrophobicinteraction chromatography, affinity chromatography, hydroxylapatitechromatography and lectin chromatography. Most preferably, highperformance liquid chromatography (“HPLC”) may be employed forpurification.

In another embodiment, therapeutic agents can be produced usingbacterial lysates in cell-free expression systems that are well known inthe art. Commercially available examples of cell-free protein synthesissystems include the EasyXpress System (commercially available fromQiagen, Inc., Valencia, Calif.).

Therapeutics also can be recovered from products of chemical syntheticprocedures and products produced by recombinant techniques from aprokaryotic or eukaryotic host, including, for example, bacterial,yeast, higher plant, insect, and mammalian cells.

Depending upon the host employed in a recombinant production procedure,therapeutics may be glycosylated or may be non-glycosylated. Inaddition, therapeutics also may include an initial modified methionineresidue, in some cases as a result of host-mediated processes. Thus, itis known that the N-terminal methionine encoded by the translationinitiation codon generally is removed with high efficiency from anyprotein after translation in all eukaryotic cells. While the N-terminalmethionine on most proteins also is efficiently removed in mostprokaryotes, for some proteins, this prokaryotic removal process isinefficient, depending on the nature of the amino acid to which theN-terminal methionine is covalently linked.

Therapeutics also may be isolated from natural sources of polypeptide.Therapeutics may be purified from tissue sources, preferably mammaliantissue sources, using conventional physical, immunological and chemicalseparation techniques known to those of skill in the art. Appropriatetissue sources for the desired therapeutics, or other techniques forobtaining the recited therapeutics such as PCR techniques, are known orare available to those of skill in the art.

Embodiment of the invention also provide a method of treating a diseaseor disorder associated with the spine. The method comprises providing aselectively expandable composite intervertebral disc prosthesis asdescribed herein. The prosthesis may be dehydrated in order to attain asmaller volume and reduced profile. Then, the prosthesis may be insertedinto an intervertebral disc space and allowed to re-hydrate therein inorder to expand and reach a final configuration. A suitable method ofdelivering or implanting a prosthesis according to embodiments of theinvention is described in, for example, U.S. Patent ApplicationPublication No. 2004/0117019 (application Ser. No. 10/717,687), thedisclosure of which is incorporated by reference herein in its entirety.

In one embodiment of the invention, a dysfunctional intervertebral discis accessed surgically, preferably using minimally invasive techniques,and at least a portion of the native nucleus pulposus material and anyfree disc fragments are removed. Subsequently, the selectivelyexpandable composite intervertebral disc prosthesis may be delivered tothe at least partially evacuated disc space. Delivery of the prosthesisto the at least partially evacuated disc space preferably may beachieved, for example, using minimally invasive surgical techniques anddevices. For example, a prosthesis according to embodiments of theinvention may be delivered via a cannula to the at least partiallyevacuated disc space. Dehydration of the prosthesis prior toimplantation may facilitate the use of minimally invasive surgicaltechniques because dehydration may reduce the volume and profile of theprosthesis. Alternatively, the prosthesis may be delivered to the atleast partially evacuated disc space in a more direct manner absent acannula. The appropriate delivery method may be selected by a suitablyskilled surgeon.

Upon implantation, the selectively expandable composite intervertebraldisc prosthesis may be re-hydrated by endogenous fluids in the body.Alternatively, a hydrating fluid may be delivered to the implantedprosthesis in order to aid hydration. Appropriate hydrating fluidsinclude, but are not limited to, water, saline solution, andcalcium-phosphate based solutions. During re-hydration, the prosthesismay selectively expand to reach its final configuration. In a preferredembodiment, the selectively expandable composite prosthesis expands to agreater height in its anterior than its posterior portion, or visaversa. This may be advantageous in order to correct or maintaincurvature of the section of the spine in which the prosthesis is to beimplanted.

In a preferred embodiment, following hydration of the selectivelyexpandable intervertebral disc prosthesis, the hydrated prosthesissubstantially fills the at least partially evacuated cavity of theintervertebral disc space. In order to accomplish this, it may bedesirable to measure the volume of the intervertebral disc space priorto implantation of the prosthesis. Following measurement, a prosthesiswith a hydrated volume substantially similar to the volume of theintervertebral disc space may be chosen for implantation. Theintervertebral disc prosthesis preferably occupies at least 50% of theevacuated intervertebral disc space, more preferably 70% of theevacuated intervertebral disc space, even more preferably 80% of theintervertebral disc space, even more preferably 90% of the evacuatedintervertebral disc space, and most preferably 99% or more of theevacuated intervertebral disc space following expansion.

Besides the volume of the intervertebral disc space in which theprosthesis is to be implanted, other dimensions such as the disc spaceheight and width may be measured in order to choose a prosthesis of thecorrect size and geometry for the disc space. The size of theselectively expandable prosthesis, when fully hydrated, can be variedfor different individuals. A typical size of an adult intervertebraldisc is roughly about 3.5 cm in the semi-minor axis, about 5.5 cm in thesemi-major axis and about 1.2 cm in thickness. The embodimentscontemplate numerous sizes for the prosthesis to accommodate differentsizes of individual patients, relative to the typical size set forthabove. Using the guidelines provided herein, skilled artisans arecapable of determining an appropriately sized prosthesis, depending onthe size and age of the patient, as well as on the amount of discmaterial removed or evacuated from the disc space.

In a preferred embodiment, the selectively expandable compositestructure may be impregnated with a radiopaque material or solutionprior to implantation. Alternatively, the composite structure maycomprise radiopaque markers embedded therein or attached to its surface.Radiopaque materials, solutions, and markers may be useful to aid inpositioning or orienting of the device during and followingimplantation. For example, the region in which the composite structureis to be implanted (e.g., the intervertebral disc space) may befluoroscopically imaged during the implantation procedure in order todetermine how the device's position and orientation. Then, the positionor orientation of the device may be altered if it is found that thedevice is not yet positioned or oriented correctly. The process ofimaging and re-positioning may be repeated as needed until the compositestructure is correctly situated in the implantation region.

In one embodiment, the selectively expandable intervertebral discprosthesis is useful in the replacement of native nucleus pulposusmaterials. In another embodiment, the prosthesis is useful in theprevention or treatment, or for aiding in the prevention or treatment,of diseases and/or disorders associated with the spinal column.Non-limiting examples of diseases and/or disorders that the prosthesesprovided by embodiments of the invention are useful in preventing ortreating include, but are not limited to: bulging disc(s); herniateddisc(s); spinal injury due to trauma; age-related degeneration orfailure of spinal column components (namely intervertebral disc(s));spinal instability; discogenic back pain; intervertebralosteochondrosis; spondylolisthesis; spinal infection; spinal tumors; andarthritis of the spine.

In an additional embodiment, the selectively expandable intervertebraldisc prostheses are packaged in kits under sterile conditions prior toimplantation into a patient. The prostheses may be included as acomponent of a surgical kit for implanting the device, along with othersurgical tools or instruments. Preferably, the kit comprises theselectively expandable prosthesis together with a minimally invasivedelivery apparatus or system.

The invention will now be described in more detail with reference to thefollowing prophetic example.

EXAMPLE

A selectively expandable composite structure according to FIG. 4,embodiments A and B, may be provided. The composite structure maycomprise a hydrophilic core 42 inside of an outer shell having adifferential composition. The top 44 a and bottom 44 b of the outershell may be comprised of a ultra high molecular weight polyethylene(UHMWPE). These surfaces may act as articulating surfaces. The peripheryor sides of the outer shell 43 may be comprised of a more elasticcomposition. Metallic endplates 40 a and 40 b may be provided to act asvertebral endplate engaging plates. Upon hydration, the more elasticperiphery of the outer shell 43 may allow the hydrophilic core 42 toexpand, thereby increasing the height of the device and pushing theendplates 40 a and 40 b against the adjacent vertebrae.

The foregoing detailed description is provided to describe the inventionin detail, and is not intended to limit the invention. Those skilled inthe art will appreciate that various modifications may be made to theinvention without departing significantly from the spirit and scopethereof.

1. A selectively expandable composite intervertebral disc prosthesis,comprising: an outer shell comprised of a non-hydrogel polymer material;at least one core positioned within the outer shell, the core comprisedof a hydrophilic polymer; and at least one conduit comprised of ahydrophilic polymer that connects the at least one core with the surfaceof the prosthesis; where the at least one core expands upon hydration,thereby deforming the outer shell.
 2. The device of claim 1, wherein theouter shell comprises a plurality of perforations of sufficient size andnumber to permit fluids to percolate through the shell and contact atleast a portion of the at least one core.
 3. (canceled)
 4. The device ofclaim 1, wherein the outer shell is at least partially porous.
 5. Thedevice of claim 1, further comprising a hydrophilic component in theouter shell.
 6. The device of claim 5, wherein the hydrophilic componentin the outer shell is selected from the group consisting of polyvinylalcohol, polyacrylic acid, poly(acrylonitrile-acrylic acid),polyacrylamides, poly(N-vinyl-2-pyrrolidone), polyurethanes,polyethylene glycol, polyethyleneoxide, poly(N-vinyl-2-pyrrolidone),polyacrylates, poly(2-hydroxy ethyl methacrylate), copolymers ofacrylates with N-vinyl pyrrolidone, N-vinyl lactams, acrylamide, andmixtures and combinations thereof.
 7. The device of claim 1, wherein theouter shell is comprised of a material selected from the groupconsisting of silicone, polyurethanes, silicone polyurethane copolymers,polyolefins, thermoplastic elastomers, thermoset elastomers,thermoplastic polymers, thermoset polymers, polybutadiene,polyisobutylene, polyisoprene, neoprene, nitrile, vulcanized rubber, andmixtures and combinations thereof.
 8. The device of claim 7, wherein theouter shell is comprised of a thermoplastic silicone polyurethanecopolymer.
 9. The device of claim 8, wherein the thermoplastic siliconepolyurethane copolymer is selected from the group consisting of siliconepolyetherurethanes; silicone polycarbonateurethane; siliconepoly(tetramethylene-oxide) (PTMO) polyether-based aromatic siliconepolyurethanes; silicone PTMO polyether-based aliphatic polyurethanes;silicone polyurethane ureas; and mixtures and combinations thereof. 10.The device of claim 1, wherein the hydrophilic polymer is selected fromthe group consisting of polyacrylamide; polyacrylic acid;polyvinylpyrrolidone; copolymers of ethyleneoxide and propyleneoxide orhyaluronic acid; collagen; gelatin; albumin; keratin; elastin; silk;hyaluronic acid and derivatives thereof; proteoglycan; glucomannan gel;polysaccharides; polyelectrolytes; and mixtures and combinationsthereof.
 11. The device of claim 10, wherein the polyelectrolytes areselected from the group consisting of proteins, nucleic acids,sulfonated styrene, polyacrylic acids, carboxymethylcellulose,polyacrylic acid, xantham gum, pectins, polystyrene sulfate,polymethacrylic acid, polyallylamine hydrochloride, carrageenan, andmixtures and combinations thereof.
 12. The device of claim 1, whereinthe hydrophilic polymer is selected from the group consisting ofpolyvinyl alcohol, polyacrylic acid, poly(acrylonitrile-acrylic acid),polyacrylamides, poly(N-vinyl-2-pyrrolidone), polyurethanes,polyethylene glycol, polyethyleneoxide, poly(N-vinyl-2-pyrrolidone),polyacrylates, poly(2-hydroxy ethyl methacrylate), copolymers ofacrylates with N-vinyl pyrrolidone, N-vinyl lactams, acrylamide, andmixtures and combinations thereof.
 13. The device of claim 1, furthercomprising at least one additive impregnated in the core, wherein theadditive is selected from the group consisting of sodium chloride,calcium chloride, magnesium chloride, magnesium sulfate, potassiumsulfate, potassium chloride, sodium sulfate, sodium acetate, ammoniumphosphate, ammonium sulfate, calcium lactate, magnesium succinate,sucrose, glucose, and fructose.
 14. The device of claim 1, wherein theprosthesis has a height within the range of from about 3 millimeters toabout 15 millimeters.
 15. The device of claim 1, wherein the prosthesishas a volume within the range of from about 0.5 milliliters to about 8milliliters.
 16. The device of claim 1, wherein the outer shell issubstantially deformable in a direction parallel to the spine duringexpansion of the at least one core, and substantially less deformable ina direction perpendicular to the spine during expansion of the at leastone core, when the device is oriented in its intended implantedorientation.
 17. The device of claim 1, wherein the modulus ofelasticity of the outer shell varies depending upon its position in thedevice.
 18. The device of claim 1, wherein the thickness of the outershell varies depending upon its position in the device.
 19. The deviceof claim 1, wherein the composition of material comprising the outershell varies depending upon its position in the device.
 20. The deviceof claim 1, wherein one or more reinforcing elements selected from thegroup consisting of metallic, polymeric, ceramic, carbon fibers, mesh,and fabrics are positioned at or in portions of the outer shell whereexpansion is desired to be limited.
 21. The device of claim 1, whereinthe at least one core is in a physical configuration selected from thegroup consisting of a single piece, multiple pieces, chunks, granules,flakes, pellets, cylinders, strips, spheres, microspheres, powders,beads, capsules, particulates, and mixtures and combinations thereof.22. The device of claim 1, wherein at least a portion of the core isporous, and the porous portion of the core comprises no more that about75% by volume of voids.
 23. The device of claim 1, wherein the volume ofthe device following hydration is no more that about three times thevolume of the device in a de-hydrated state.
 24. The device of claim 1,further comprising vertebral endplate contacting elements attached tothe top and bottom of the device.
 25. The device of claim 1, wherein thecross-sectional shape of the device is selected from the groupconsisting of kidney-shaped, C-shaped, oval-like, spherical,rectangular, square, cylindrical, capsule, U-shaped, V-shaped, X-shaped,and “O” or donut shaped.
 26. The device of claim 1, further comprisingat least one therapeutic agent, pharmaceutical agent, or growth factorimpregnated in the core.
 27. The device of claim 1, further comprisingat least one therapeutic agent, pharmaceutical agent, or growth factorimpregnated in or coated on the outer shell.
 28. The device of claim 1,further comprising a radiopaque material or solution impregnated in thedevice.
 29. The device of claim 1, further comprising a radiopaquemarker embedded in the device or attached to its surface.
 30. A methodof treating or preventing a disease or disorder associated with thespine, comprising: providing a selectively expandable compositeintervertebral disc prosthesis as in claim 1; substantially dehydratingthe prosthesis; inserting the prosthesis into an intervertebral discspace; and allowing the prosthesis to re-hydrate in the intervertebraldisc space.
 31. The method of claim 30, wherein the prosthesis shrinksupon dehydration and expands upon re-hydration.
 32. The method of claim30, wherein the prosthesis expands to a greater height upon re-hydrationin its anterior portion than in its posterior portion.
 33. The method ofclaim 30, further comprising delivering a material selected from thegroup consisting of water or saline solution to the prosthesis followinginsertion.
 34. The method of claim 33, further comprising mixing withthe water or saline solution a material selected from the groupconsisting of radiopaque agents, therapeutic agents, growth factors,pharmaceutical agents, and mixtures and combinations thereof.
 35. Themethod of claim 30, further comprising surgically evacuating at least aportion of the nucleus pulposus material and any free disc fragmentsfrom the intervertebral disc space prior to inserting the prosthesisinto the intervertebral disc space.
 36. The method of claim 30, furthercomprising measuring the volume of the intervertebral disc space priorto inserting the prosthesis into the intervertebral disc space.
 37. Themethod of claim 30, wherein inserting the prosthesis is accomplished bythe use of minimally invasive surgical techniques.
 38. The method ofclaim 30, wherein the disease or disorder is selected from the groupconsisting of: bulging discs; herniated discs; spinal injury due totrauma; age-related degeneration or failure of spinal column components;spinal instability; discogenic back pain; intervertebralosteochondrosis; spondylolisthesis; spinal infection; spinal tumors;arthritis of the spine; and combinations thereof.
 39. A selectivelyexpandable composite intervertebral disc prosthesis, comprising: anouter shell comprised of a non-hydrogel polymer material; and at leastone core positioned within the outer shell, the core comprised of ahydrophilic polymer; where at least a portion of the core is porous, andthe porous portion of the core comprises no more that about 75% byvolume of voids; and where the at least one core expands upon hydration,thereby deforming the outer shell.
 40. A method of treating orpreventing a disease or disorder associated with the spine, comprising:providing a selectively expandable composite intervertebral discprosthesis as in claim 39; substantially dehydrating the prosthesis;inserting the prosthesis into an intervertebral disc space; and allowingthe prosthesis to re-hydrate in the intervertebral disc space.